Controlled exposure of in-vivo sensors

ABSTRACT

A method of protecting an in-vivo sensor includes forming a sensing surface on a surface of the in-vivo sensor, the sensing surface including a functionalized monolayer that will bind to an analyte of interest; and coating the sensing surface of the sensor with a bioabsorbable polymeric coating including a bioabsorbable polymer; wherein the bioabsorbable polymeric coating is configured to protect the in-vivo sensor until needed for implantation.

DOMESTIC PRIORITY

This present application is a divisional of U.S. patent application Ser.No. 15/953,885, filed on Apr. 16, 2018, which is a continuation of U.S.patent application Ser. No. 15/340,180, filed on Nov. 1, 2016, now U.S.Pat. No. 9,999,899, which is hereby incorporated herein by reference inits entirety.

BACKGROUND

Embodiments of the present invention relate to sensors, and morespecifically, to controlled in-vivo sensors.

In-vivo chemical sensors are attractive areas of research in medicaldevice manufacturing and development. Generally, fabrication of suchchemical sensors includes coating a surface of a sensor with a marker,such as a protein, aptamer, deoxyribonucleic acid (DNA) segment, or someother biomarker. The marker then attaches to the desired analyte ofinterest, for example, a protein of interest, and the signal is thentransduced with a device, such as a transistor. The sensors can includeadditional “non-fouling compounds” that prevent the nonspecific bindingof undesired proteins.

SUMMARY

According to an embodiment, a method of protecting an in-vivo sensorincludes forming a sensing surface on a surface of the in-vivo sensor,the sensing surface including a functionalized monolayer that will bindto an analyte of interest; and coating the sensing surface of the sensorwith a bioabsorbable polymeric coating including a bioabsorbablepolymer; wherein the bioabsorbable polymeric coating is configured toprotect the in-vivo sensor until needed for implantation.

According to another embodiment, a method of fabricating a controlledin-vivo sensor includes forming a sensing surface on a surface of asensor, the sensing surface including a functionalized monolayer thatwill bind to an analyte of interest; and coating the sensing surface ofthe sensor with a bioabsorbable polymeric coating including abioabsorbable polymer; wherein the controlled in-vivo sensor isconfigured to be implantable into a living animal, and the bioabsorbablepolymeric coating is configured to desorb after being implanted andexposed to a biological environment.

Yet, according to another embodiment, a controlled in-vivo sensorincludes a sensing surface including a functionalized monolayerconfigured to bind to an analyte of interest; and a bioabsorbablepolymeric coating including a bioabsorbable polymer configured toprotect the sensing surface until the controlled in-vivo sensor isimplanted and exposed to a biological environment of a living animal.

BRIEF DESCRIPTION OF THE DRAWINGS

The subject matter which is regarded as embodiments of the invention isparticularly pointed out and distinctly claimed in the claims at theconclusion of the specification. The foregoing and other features, andadvantages of the embodiments of the invention are apparent from thefollowing detailed description taken in conjunction with theaccompanying drawings in which:

FIGS. 1-3 illustrate exemplary methods of controlled in-vivo sensingaccording to embodiments, in which:

FIG. 1 is a cross-sectional side view after forming a sensing surface ona surface of a sensor;

FIG. 2 is a cross-sectional side view after disposing a bioabsorbablepolymer on the sensing surface;

FIG. 3 is a cross-sectional side view of the sensor after beingimplanted into a living animal for a period of time;

FIG. 4A is a cross-sectional side view of a controlled in-vivo sensoraccording to embodiments;

FIG. 4B is a cross-sectional side view of the controlled in-vivo sensorafter implantation and removal of the bioabsorbable polymer layer;

FIG. 5A is a cross-sectional side view of a controlled in-vivo sensorwith several sensors according to embodiments;

FIG. 5B is a cross-sectional side view of the controlled in-vivo sensorafter implantation and removal of the upper bioabsorbable polymer layer;

FIG. 5C is a cross-sectional side view of the controlled in-vivo sensorafter implantation and removal of the middle bioabsorbable polymerlayer;

FIG. 5D is a cross-sectional side view of the controlled in-vivo sensorafter implantation and removal of the bottom bioabsorbable polymerlayer;

FIG. 6 illustrates a flow diagram of a method for controlled in vivosensing according to embodiments;

FIG. 7 is a flow diagram of a method for controlled in vivo sensingaccording to embodiments; and

FIG. 8 is a cross-sectional side view of a controlled in-vivo sensoraccording to embodiments.

DETAILED DESCRIPTION

Embodiments of the present invention are described herein with referenceto the related drawings. Alternative embodiments can be devised withoutdeparting from the scope of this invention. It is noted that variousconnections and positional relationships (e.g., over, below, adjacent,etc.) are set forth between elements in the following description and inthe drawings. These connections and/or positional relationships, unlessspecified otherwise, can be direct or indirect, and the presentinvention is not intended to be limiting in this respect. Accordingly, acoupling of entities can refer to either a direct or an indirectcoupling, and a positional relationship between entities can be a director indirect positional relationship. As an example of an indirectpositional relationship, references in the present description toforming layer “A” over layer “B” include situations in which one or moreintermediate layers (e.g., layer “C”) is between layer “A” and layer “B”as long as the relevant characteristics and functionalities of layer “A”and layer “B” are not substantially changed by the intermediatelayer(s).

The following definitions and abbreviations are to be used for theinterpretation of the claims and the specification. As used herein, theterms “comprises,” “comprising,” “includes,” “including,” “has,”“having,” “contains” or “containing,” or any other variation thereof,are intended to cover a non-exclusive inclusion. For example, acomposition, a mixture, process, method, article, or apparatus thatcomprises a list of elements is not necessarily limited to only thoseelements but can include other elements not expressly listed or inherentto such composition, mixture, process, method, article, or apparatus.

Additionally, the term “exemplary” is used herein to mean “serving as anexample, instance or illustration.” Any embodiment or design describedherein as “exemplary” is not necessarily to be construed as preferred oradvantageous over other embodiments or designs. The terms “at least one”and “one or more” are understood to include any integer number greaterthan or equal to one, i.e. one, two, three, four, etc. The terms “aplurality” are understood to include any integer number greater than orequal to two, i.e. two, three, four, five, etc. The term “connection”can include an indirect “connection” and a direct “connection.”

References in the specification to “one embodiment,” “an embodiment,”“an example embodiment,” etc., indicate that the embodiment describedcan include a particular feature, structure, or characteristic, butevery embodiment may or may not include the particular feature,structure, or characteristic. Moreover, such phrases are not necessarilyreferring to the same embodiment. Further, when a particular feature,structure, or characteristic is described in connection with anembodiment, it is submitted that it is within the knowledge of oneskilled in the art to affect such feature, structure, or characteristicin connection with other embodiments whether or not explicitlydescribed.

For purposes of the description hereinafter, the terms “upper,” “lower,”“right,” “left,” “vertical,” “horizontal,” “top,” “bottom,” andderivatives thereof shall relate to the described structures andmethods, as oriented in the drawing figures. The terms “overlying,”“atop,” “on top,” “positioned on” or “positioned atop” mean that a firstelement, such as a first structure, is present on a second element, suchas a second structure, wherein intervening elements such as an interfacestructure can be present between the first element and the secondelement. The term “direct contact” means that a first element, such as afirst structure, and a second element, such as a second structure, areconnected without any intermediary conducting, insulating orsemiconductor layers at the interface of the two elements. It should benoted that the term “selective to,” such as, for example, “a firstelement selective to a second element,” means that the first element canbe etched and the second element can act as an etch stop.

As used herein, the terms “about,” “substantially,” “approximately,” andvariations thereof are intended to include the degree of errorassociated with measurement of the particular quantity based upon theequipment available at the time of filing the application. For example,“about” can include a range of ±8% or 5%, or 2% of a given value.

For the sake of brevity, conventional techniques related tosemiconductor device and integrated circuit (IC) fabrication may or maynot be described in detail herein. Moreover, the various tasks andprocess steps described herein can be incorporated into a morecomprehensive procedure or process having additional steps orfunctionality not described in detail herein. In particular, varioussteps in the manufacture of semiconductor devices andsemiconductor-based ICs are well known and so, in the interest ofbrevity, many conventional steps will only be mentioned briefly hereinor will be omitted entirely without providing the well-known processdetails.

Turning now to a description of technologies that are more specificallyrelevant to aspects of the present invention, embodiments herein aredirected to in-vivo sensing, as mentioned above. Prior to implantationinto the body of a living animal, the in-vivo sensor is initiallysterilized to prevent infection. The sensors have finite lifetimes, forexample hours or days, after which time the sensor can becomenon-functional, whether or not they are exposed to a biologicalenvironment.

There are two challenges that can be associated with such in-vivosensors. First, in-vivo sensors can be challenging to sterilize becausethin organic films arranged on their surfaces can be unstable understerilization conditions. Second, although “non-fouling” coatings can beincorporated into the sensors to delay deterioration of a functionalsensor, the sensor surfaces can nonetheless foul over time.

Accordingly, described herein are methods of fabricating in-vivo sensorswith a bioabsorbable coating that is configured to desorb over apredetermined and controlled period of time. The bioabsorbable coatingallows for the introduction of new sensors at some time afterimplantation. The bioabsorbable coating also allows for sterilization,as the coating protects the organic films arranged beneath. According toembodiments, the bioabsorbable coating thickness and composition arecontrolled to expose the sensor to the in-vivo environment at controlledtimes after implantation.

Turning now to the figures, FIGS. 1 and 2 illustrate methods offabricating an in-vivo sensor 100. Sensor 100 includes a substrate 101with a sensing surface 102 arranged on the substrate 101. In FIG. 1, asensing surface 102 is formed on substrate 101. The substrate 101 caninclude, but is not limited to, metals, metal alloys, semiconductors,insulators, or a combination thereof. In an exemplary embodiment, thesubstrate 101 includes a gold film.

The sensing surface 102 includes a monolayer 103 arranged on a surfaceof the substrate 101. The monolayer 103 includes a functional group thatis bound to the substrate 101. For example, when the substrate 101 is agold film, the monolayer 103 can include a thiolated end group thatbonds to the substrate 101. The monolayer 103 includes a polymer thatextends from a surface of the substrate 101 to a chemical moiety 104.

The monolayer 103 can include any polymer or copolymer. The monolayer103 can include hydrophobic polymers, such as polysiloxane, and/orhydrophilic polymers, such as polyuria and polyurethane. The monolayer103 can include a blend of two or more polymers, each of which caninclude a combination of two or more polymers with differentcharacteristics, including combinations of hydrophobic and hydrophilicpolymers. In embodiments, the monolayer 103 includes polyethylene glycol(PEG). In other embodiments, the hydrophilic polymer includes acopolymer of polypropylene glycol and PEG.

The monolayer 103 is functionalized with chemical moiety 104. Chemicalmoiety 104 can be, but is not limited to, a protein, an antibody, anaptamer, a DNA segment, an RNA segment, a chemical compound, or acombination thereof. The chemical moiety 104 extends from the surface ofthe monolayer 103. The chemical moiety 104 can be any compound ormolecule that can attach to the monolayer 103 and bond or interact withan analyte of interest once introduced into the body of a living animal.

The monolayer 103 functionalized with the chemical moiety 104 forms athin organic film on a surface of the substrate 101. The monolayer 103can have a thickness that generally varies and is not intended to belimited. In some embodiments, the monolayer 103 has a thickness in arange from about 0.5 to about 50 nm. In other embodiments, the monolayer103 has a thickness in a range from about 10 to about 15 nm. Yet, inother embodiments, the monolayer 103 has a thickness outside of theseranges.

The sensor 100 can be any type of implantable sensor. The sensor 100 canbe, for example, a chemical or biochemical sensor. The sensor 100 isconfigured to be implanted in a living animal (such as a living human).The sensor 100 can be configured for detection or continuous monitoringof an analyte of interest, such as glucose, oxygen, cardiac markers, lowdensity lipoprotein, high density lipoprotein, or triglycerides. Thesensor 100 can be configured to monitor for pathogen, such as forexample, bacteria (e.g., methicillin resistant Staphylococcus aureus(MRSA)) or viruses.

FIG. 2 is a cross-sectional side view after disposing a bioabsorbablepolymer layer 210 on the sensing surface 102. The bioabsorbable polymerlayer 210 is a coating that includes a bioabsorbable polymer. Thebioabsorbable polymer layer 210 covers the sensing surface 102 andprotects the sensing surface 102 during subsequent sterilization priorto implantation in a living animal. The bioabsorbable polymer layer 210protects the thin organic films of the functionalized monolayer 103 fromthe high temperature and pressure of the sterilization conditions.

The thickness of the bioabsorable polymer layer 210 is not intended tobe limited and can be tailored as desired. The bioabsorbable polymerlayer 210 compositions and thickness can be tailored and controlled sothat they desorb over time after being implanted in a living animal.Such control allows for the “introduction” of new sensors after a giventime following initial implantation. The sensor 100 can then be exposedto the biological environment after implantation at controlled times.

In some embodiments, the thickness of the bioabsorbable polymer layer210 is in a range from about 50 to about 1000 nm. In other embodiments,the thickness of the bioabsorbable polymer layer 210 is in a range fromabout 200 to about 300 nm.

The composition of the bioabsorbable polymer layer 210 can also betailored as desired and is not intended to be limited. The bioabsorbablepolymer of the layer 210 can include a bioabsorbable polymer. Thepolymer can include, but is not limited to, lactic acid, glycolic acid,glucose, polytrimethylene carbonate, collagen, laminin, hydroxyapatite,hyaluronan, and/or amino acids. In some embodiments, the polymer caninclude one or more linear polyesters such as, for example,polycaprolactone, poly-ester-ethers (such as polydioxanone), polyaminoacids (such as poly-glutamate, poly-lysine, poly-leucine),poly-anhydrides (such as polysebacic acid), including derivatives,copolymers, and any combination thereof. The polymer can be across-linking polymer in some embodiments. In embodiments, the polymeris poly lactic acid.

The bioabsorbable polymer layer 210 covers the sensing surface 102 andcan be deposited by any methods, which depend on the composition anddesired thickness of the layer itself. In some embodiments, thebioabsorbable polymer layer 210 can be deposited by spin coating ontothe sensing surface 102 of the sensor 100.

For simplicity, only a cut away portion of the sensor 100 is beingshown. The size, shape, and dimensions of the sensor 100 can generallyvary and depends on the particular application, for example, where thesensor will be implanted and the desired sensing function. Therefore,the sensor 100 can have any desired size, shape, and dimensions.

Once the sensor 100 is formed with the bioabsorbable polymer layer 210,the sensor 100 is sterilized. The sensor 100 can be sterilized underconditions suitable to render the sensor 100 sterile. The sensor 100 canbe sterilized, for example, under elevated temperature and high pressureconditions. The sensor 100 can be sterilized under high pressuresaturated steam at high temperatures. The sensor 100 can be sterilizedusing industrial instrumentation, such as an autoclave machine. Thecomposition and thickness of the bioabsorbable polymer layer 210 iscontrolled such that the sensor 100 can withstand the sterilizationconditions necessary to sterilize the sensor 100 before being implantedinto the living animal.

Although non-fouling compounds can be generally incorporated inimplantable sensors to prevent non-specific binding of undesiredanalytes, even non-fouling compounds foul over time. Fouling, ordeterioration of the non-fouling compounds over time, can result innon-specific binding of undesired analytes to the sensor. Thenon-fouling compounds also cannot protect the thin organic layers of thesensor during sterilization.

FIG. 3 is a cross-sectional side view of the sensor 100 after beingimplanted into a living animal for a period of time. The sensor 100 canbe implanted into a living animal's arm, wrist, leg, abdomen,peritoneum, or other region suitable for sensor implantation. The sensor100 can be implanted beneath the skin, such as in the subcutaneous orperitoneal tissue. The living animal can be a human or any other livinganimal, such as a mouse or rabbit.

After being implanted in the living animal, the bioabsorbable polymerlayer 210 desorbs (dissolves or is at least partially removed from thesurface of the sensor) over a period of time. Because the thickness andcomposition of the bioabsorbable polymer layer 210 can be tailored andcontrolled to desorb over a known and controlled period of time, thesensor 100 with the functionalized monolayer 103 (sensing surface 102)is exposed to the biological environment to be sensed at a controlledperiod of time.

Once a sensor without any protection is implanted in a living animal andexposed to the biological environment of the living animal, the sensorwill eventually foul, or deteriorate. Even an unexposed sensor, beforeimplantation, will eventually foul or deteriorate over time.

The bioabsorbable polymer layer 210, however, will slowly desorb ordissolve over a controlled period of time to expose the sensing surface102 of the sensor to the biological environment. Similar to dissolvablesutures, for example, the bioabsorbable polymer layer 210 will dissolveor be removed to expose the sensing surface 102 after a known periodtime. The bioabsorable polymer layer 210 allows for exposure of a “new”sensor over a given and controlled time period. Thus the bioabsorbablepolymer layer 210 provides a time-released biosensor. In embodiments,different sensors can be arranged as layers of different thicknesses orarranged side-by-side. The thickness and/or composition of each sensorcan be adjusted to expose the sensors at different times.

Once the sensing surface 102 of the sensor 100 is exposed, the chemicalmoiety 104 interacts with or bonds to the analyte of interest 303. Theanalyte of interest 303 can be, but is not limited to, amino acids,proteins, peptides, sugars, carbohydrates, gas molecules, primarymetabolites, secondary metabolites, lipids, nucleotides or nucleicacids, microbes, viruses, hormones, hydrocarbons, vitamins, amides,amines, glycosides, or any combination thereof. The analyte of interest303 can be any natural biomolecule or biological byproduct formed in aliving animal or found in a living animal. After the sensor binds to theanalyte of interest, the signal is then transduced with a device, suchas a transistor.

FIG. 4A is a cross-sectional side view of a controlled in-vivo sensor400 according to embodiments. A non-fouling coating 410 is applied tothe sensing surface 102 of the sensor 400. The non-fouling coating 410provides some protection to the thin organic film of the sensor 400 andprevents non-specific binding of undesired analytes.

Examples of non-fouling coatings (or anti-fouling coatings) include, butare not limited to, zwitterionic coatings, hydrophilic polymer coatings(e.g. poly- and oligoethylene glycol, PEG and OEG), mono-, oligo- andpolysaccharide-based coatings, protein-based coatings, or coatings thatinclude a combination thereof.

The thickness of the non-fouling coating 410 generally varies and is notintended to be limited. In some embodiments, the thickness of thenon-fouling coating 410 of the sensor 400 is in a range from about 50 toabout 1000 nm. In other embodiments, the thickness of the non-foulingcoating 410 of the sensor 400 is in a range from about 400 to about 500nm. Yet, in other embodiments, the thickness of the non-fouling coating410 is not limited to the aforementioned thicknesses and can be tailoredas desired. It is noted that the thickness of the non-fouling coating410 shown in FIG. 4 is for representation purposes only and is notintended to drawn to scale.

After depositing the non-fouling coating 410 on the sensing surface 102,a bioabsorbable polymer layer 420 is deposited on the surface of thesensor 400. The bioabsorbable polymer layer 420 is disposed on top ofthe non-fouling coating 410, which protects both the non-fouling coating410 and any exposed areas of the sensing surface 102. The compositionand thickness of the bioabsorbable polymer layer 420 is described abovewith reference to FIG. 2.

The bioabsorbable polymer layer 420 can be sterilized and then implantedin a living animal as described above with reference to FIG. 3. Thebioabsorbable polymer layer 420 protects the non-fouling coating 410from the harsh conditions that the sensor 400 is subjected to duringsterilization.

After the sensor is then implanted into the living animal, thebioabsorbable polymer layer 420 will then dissolve or be removed fromthe surface of the sensor 400 to expose the non-fouling coating 420and/or the sensing surface 102 after a known period of time, as shown inFIG. 4B.

FIG. 5A is a cross-sectional side view of a controlled in vivo sensor500 according to embodiments. In-vivo sensor 500 includes a sensingsurface 530 with several different sensors extending from the monolayer103. The sensing surface 530 includes a first chemical moiety 504 (firstsensor), a second chemical moiety 505 (second sensor), and thirdchemical moiety 506 (third sensor). Several layers of bioabsorbablepolymers, or a thick layer of a single bioabsorbable polymer that coversall three sensors (first, second, and third sensors). Although firstsensor, second sensor, and third sensor are shown as being arrangedacross the entire substrate, each sensor can be arranged side-by-side.Each sensor can have different thicknesses and/or compositions such thatthe sensors are exposed at different times.

First bioabsorbable polymer layer 510 covers the first sensor (firstchemical moiety 504). Second bioabsorbable polymer layer 511 covers thesecond sensor (second chemical moiety 505). Third bioabsorbable polymerlayer 512 covers the third sensor 506 (third chemical moiety).

After the sensor 500 is then implanted into the living animal, the upperbioabsorbable polymer layer (third bioabsorbable polymer layer 512) isremoved over time, or dissolved to expose third sensor 506 of thesensing surface 530, as shown in FIG. 5B. Exposure of the third sensoroccurs initially over a known period of time.

Then, after a longer period of time, the next/middle bioabsorbablepolymer layer (second bioabsorbable polymer layer 511) is removed overtime, or dissolved to expose second sensor 505 of the sensing surface530, as shown in FIG. 5C.

Then, after an even longer period of time, the bottom/last bioabsorbablepolymer layer (first bioabsorbable polymer layer 510) is removed overtime, or dissolved to expose first sensor 504 of the sensing surface530, as shown in FIG. 5C.

Thus, by staggering different sensors and bioabsorbable polymer layerson a single sensing surface, new and different sensors can be exposedover a staggered period of time. For example, different sensors can beexposed at, for example, day 1, day 7, day 14, day 21, etc. Suchstaggering allows for long-term monitoring in-vivo and mitigates theproblem of sensor fouling. Although three sensors are shown in FIGS.5A-5D, the controlled in-vivo sensors described herein can include anynumber of sensors and layers.

Although the compositions of the bioabsorbable polymer layers can bedifferent in composition, in some embodiments first bioabsorbablepolymer layer 510, second bioabsorbable polymer layer 511, and thirdbioabsorbable polymer layer 512 are the same polymeric composition. Whenthe compositions are the same, different sensors are still exposed overa staggered period of time as the polymer layers desorb or dissolve togradually expose the sensing surface.

Although not shown, additional non-fouling coatings can be included inthe sensor 500. The non-fouling coatings are described above withreference to FIG. 4A and can be disposed beneath the bioabsorbablepolymer layers.

FIG. 6 illustrates a flow diagram of a method for controlled in vivosensing according to embodiments. In box 601, the method includesfabricating a controlled in-vivo sensor. Various in-vivo sensors aredescribed above. In box 602, the method includes implanting thecontrolled in-vivo sensor in a living animal. In box 603, the methodincludes sensing an analyte of interest over time using the controlledin-vivo sensor.

FIG. 7 is a flow diagram of a method for controlled in vivo sensingaccording to embodiments. In box 701, the method includes coating asensing surface of a sensor with a bioabsorbable polymer. In box 702,the method includes sterilizing the sensor. In box 703, the methodincludes implanting the sensor in a living animal. In box 704, themethod includes sensing an analyte.

FIG. 8 is a cross-sectional side view of a controlled in-vivo sensor 800according to embodiments. The sensor 800 includes a substrate 801 and asensing surface 802. In an exemplary embodiment, the substrate 801includes a metal film, such as a gold or silver film.

The sensing surface 802 includes an organic monolayer. The organicmonolayer includes a polymer 811 extending from the surface of thesubstrate 801. The polymer 811 can be a copolymer. In exemplaryembodiments, the polymer includes PEG.

The polymer 811 is bound to the surface of the substrate 801 via a firstfunctional group 810. The first functional group 810 can be any chemicalfunctional group that can interact with the substrate 801. For example,the first functional group 810 can be a thiol group when the substrate801 is a gold film.

On the opposing end of the polymer 811 is a second functional group 812that contacts or bonds to the chemical moiety 813 that will interactwith or sense the analyte of interest once the sensor 800 is implanted.In exemplary embodiments, the chemical moiety is an antibody, such asIgG.

The descriptions of the various embodiments of the present inventionhave been presented for purposes of illustration, but are not intendedto be exhaustive or limited to the embodiments described. Manymodifications and variations will be apparent to those of ordinary skillin the art without departing from the scope and spirit of the describedembodiments. The terminology used herein was chosen to best explain theprinciples of the embodiments, the practical application or technicalimprovement over technologies found in the marketplace, or to enableothers of ordinary skill in the art to understand the embodimentsdescribed herein.

What is claimed is:
 1. A controlled in-vivo sensor comprising: a metalsubstrate; a sensing surface comprising an organic monolayer comprisinga polymer extending from the metal substrate; a first functional groupat a first end of the polymer and contacting the metal substrate; asecond functional group at a second end of the polymer to contact ananalyte of interest; and a bioabsorbable polymer layer arranged on thesensing surface.
 2. The controlled in-vivo sensor of claim 1, whereinthe metal substrate comprises silver.
 3. The controlled in-vivo sensorof claim 1, wherein the metal substrate comprises gold.
 4. Thecontrolled in-vivo sensor of claim 1, wherein the polymer comprisesfunctionalized polyethylene glycol.
 5. The controlled in-vivo sensor ofclaim 1, wherein the bioabsorbable polymer comprises lactic acid,glycolic acid, glucose, polytrimethylene carbonate, collagen, laminin,hydroxyapatite, hyaluronan, amino acid, or a combination thereof.
 6. Thecontrolled in-vivo sensor of claim 1, wherein the organic monolayer hasa thickness in a range from about 0.5 to about 50 nm.
 7. The controlledin-vivo sensor of claim 1, wherein the organic monolayer has a thicknessin a range from about 10 to about 15 nm.
 8. The controlled in-vivosensor of claim 1, wherein the controlled in-vivo sensor is configuredfor detection or continuous monitoring of glucose, oxygen, cardiacmarkers, low density lipoprotein, high density lipoprotein, ortriglycerides.
 9. The controlled in-vivo sensor of claim 1, wherein thecontrolled in-vivo sensor is configured to monitor a pathogen.
 10. Thecontrolled in vivo sensor of claim 1, wherein the bioabsorbable polymerlayer comprises polylactic acid.
 11. A controlled in-vivo sensorcomprising: a metal substrate; a sensing surface comprising an organicmonolayer comprising a polymer extending from the metal substrate; athiolated first functional group at a first end of the polymer andcontacting the metal substrate; a second functional group at a secondend of the polymer to contact an analyte of interest; and abioabsorbable polymer layer arranged on and covering the sensingsurface.
 12. The controlled in-vivo sensor of claim 11, wherein thesubstrate comprises silver.
 13. The controlled in-vivo sensor of claim11, wherein the substrate comprises gold.
 14. The controlled in-vivosensor of claim 11, wherein the polymer comprises functionalizedpolyethylene glycol.
 15. The controlled in-vivo sensor of claim 11,wherein the bioabsorbable polymer comprises lactic acid, glycolic acid,glucose, polytrimethylene carbonate, collagen, laminin, hydroxyapatite,hyaluronan, amino acid, or a combination thereof.
 16. The controlledin-vivo sensor of claim 11, wherein the organic monolayer has athickness in a range from about 0.5 to about 50 nm.
 17. The controlledin-vivo sensor of claim 11, wherein the organic monolayer has athickness in a range from about 10 to about 15 nm.
 18. The controlledin-vivo sensor of claim 11, wherein the controlled in-vivo sensor isconfigured for detection or continuous monitoring of glucose, oxygen,cardiac markers, low density lipoprotein, high density lipoprotein, ortriglycerides.
 19. The controlled in-vivo sensor of claim 11, whereinthe controlled in-vivo sensor is configured to monitor a pathogen. 20.The controlled in vivo sensor of claim 11, wherein the bioabsorbablepolymer layer comprises polylactic acid.